JP3760920B2 - Sensor - Google Patents
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- JP3760920B2 JP3760920B2 JP2003054581A JP2003054581A JP3760920B2 JP 3760920 B2 JP3760920 B2 JP 3760920B2 JP 2003054581 A JP2003054581 A JP 2003054581A JP 2003054581 A JP2003054581 A JP 2003054581A JP 3760920 B2 JP3760920 B2 JP 3760920B2
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/024—Detecting, measuring or recording pulse rate or heart rate
- A61B5/02416—Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
Description
【０００１】
【発明の属する技術分野】
本発明は、脈拍数等の生体の状態を検出するセンサに関するものである。
【０００２】
【従来の技術】
近年では、健康管理の用途で、日常生活やジョギング等の運動時において、心臓の拍動数（心拍数）をモニターするニーズが高まっている。この心拍数を検出するには、心拍に伴って発生する活動電位を胸部より計測して、即ち心電図を用いて、その振幅のピーク間隔時間から算出する方法が一般的である。
【０００３】
しかし、この方法は、電極を体に貼り付ける必要があり、その手順がわずらわしいので、最近では、より簡便な方法として、脈波を計測して脈拍数を検出する方法が考えられている。
前記脈波とは、心拍につれて起こる動脈内の圧力変動が、末梢動脈に波動として伝わったものであり、その脈波を計測する装置として、光学式脈波センサがある。
【０００４】
この光学式脈波センサは、血液中のヘモグロビンの光吸収特性を利用して、末梢動脈の血液の波動的な容積変化を計測するものであり、人体（指、腕、こめかみ等）に簡便に装着して脈波を計測することができるため、脈拍数を検出する装置として、今後も広く普及して行くと考えられる。
【０００５】
また、前記心拍数、脈拍数（拍／分）は、下記式（１）に示す様に、それぞれ６０を心電波形、脈波波形の振幅のピーク間隔時間（秒）で割った値である。
心拍数、脈拍数（拍／分）＝６０／振幅のピーク間隔時間（秒）・・・（１）
この心電波形と脈波波形の振幅のピーク位置は、図１０に示す様に、通常、同期しており、心拍数と脈拍数は一致する。
【０００６】
しかし、日常生活や運動時において、脈波センサを装着した計測部位に体動が生ずると、末梢動脈の血流が乱れ、心拍とは無関係な脈波の振幅のピークが発生し、心拍数と脈拍数は一致しなくなる。こうなると、脈拍数を心拍数の代用として利用しようとする本来の目的は達成できない。
【０００７】
また、心拍とは無関係な脈波の振幅のピークは、心拍に同期する脈波の振幅のピークの発生周波数と近いという特性があるため、通常のノイズ除去に適用されるフィルタ処理では、対策が不可能である。
この対策として、運動ノイズセンサを用いて運動ノイズによる信号を検出し、運動ノイズと脈拍信号が重なった信号から運動ノイズを除去し、運動時でも正確な脈拍を検出しようとする技術が提案されている（特許文献１参照）。
【０００８】
また、異なる波長の光を生体に照射し、それぞれで得られた信号を演算処理することにより、生体の体動波成分と血液脈動波成分を区別し、脈拍を正確に検出しようとする技術が提案されている（特許文献２参照）。
【０００９】
【特許文献１】
特開平７−２９９０４４号公報 （第２頁、図１）
【特許文献２】
特開平７−０８８０９２号公報 （第２頁、図１）
【００１０】
【発明が解決しようとする課題】
しかしながら、前記特許文献１の技術では、運動ノイズセンサを用いて運動ノイズを検出しても、皮膚の表面反射など人体に関して発生するノイズには対応できないという問題があった。
【００１１】
また、前記特許文献２の技術では、両信号に体動波成分と血液脈動波成分とが含まれ、また、センサの装着状態や個人差によって、体動波成分と血液脈動波成分の関係は変化するため、同公報に記載の一意的な演算処理では脈拍を正確に求めることができないという問題があった。
本発明は、前記課題を解決するためになされたものであり、その目的は、皮膚の表面反射、センサの装着状態、個人差等の影響を低減して、正確に脈拍等の生体の状態を検出することができるセンサを提供することにある。
【００３３】
【課題を解決するための手段及び発明の効果】
（１）請求項１の発明は、生体に対して、波長の異なる光を、それぞれ別個に照射する光照射手段と、前記光照射手段から照射された各光の反射光を受光する反射波受光手段と、を、筐体内に収容したセンサ（例えば脈波センサ）において、前記光照射手段及び前記反射波受光手段の各光の照射側及び受光側に、各光及びその反射光が透過する窓部を備えるとともに、前記長波長の光を照射する側の窓部の外側及び／又は前記長波長の光の反射波を受光する側の窓部の外側に、前記人体の皮膚から離すように引き下がり部を設けたことを特徴とするセンサを要旨とする。
【００３４】
本発明では、長波長の光（例えば赤外光）を照射する側の窓部の外側及び／又は長波長の光の反射波を受光する側の窓部の外側に、人体の皮膚から離すように引き下がり部（隙間となる部分）を設けるので、窓部の外側に皮膚が密着している箇所に比べて、皮膚の動きが容易になる。よって、例えば赤外光を用いた場合に、体動の変化を検出する能力が高いという効果がある。
【００３５】
（２）請求項２の発明は、生体に対して、波長の異なる光を、それぞれ別個に照射する光照射手段と、前記光照射手段から照射された各光の反射光を受光する反射波受光手段と、を、筐体内に収容したセンサ（例えば脈波センサ）において、前記光照射手段及び前記反射波受光手段の各光の照射側及び受光側に、各光及びその反射光が透過する窓部を備えるとともに、前記長波長の光を照射する側の窓部の外側及び／又は前記長波長の光の反射波を受光する側の窓部の外側に、凹凸を設けたことを特徴とするセンサを要旨とする。
【００３６】
本発明では、長波長の光（例えば赤外光）を照射する側の窓部の外側及び／又は長波長の光の反射波を受光する側の窓部の外側に、凹凸を設けるので、窓部の外側に皮膚が密着している箇所に比べて、皮膚の動きが容易になる。よって、例えば赤外光を用いた場合に、体動の変化を検出する能力が高いという効果がある。
【００３７】
（３）請求項３の発明は、生体に対して、波長の異なる光を、それぞれ別個に照射する光照射手段と、前記光照射手段から照射された各光の反射光を受光する反射波受光手段と、を、筐体内に収容したセンサ（例えば脈波センサ）において、前記光照射手段及び前記反射波受光手段の各光の照射側及び受光側に、各光及びその反射光が透過する窓部を備えるとともに、前記長波長の光を照射する側の窓部の外側及び／又は前記長波長の光の反射波を受光する側の窓部の外側に、透光性の柔軟な材料を配置したことを特徴とするセンサを要旨とする。
【００３８】
本発明では、長波長の光（例えば赤外光）を照射する側の窓部の外側及び／又は長波長の光の反射波を受光する側の窓部の外側に、透光性の柔軟な材料からなる部材を配置するので、硬質の窓部の外側に皮膚が密着している箇所に比べて、皮膚の動きが容易になる。よって、例えば赤外光を用いた場合に、体動の変化を検出する能力が高いという効果がある。
【００３９】
（４）請求項４の発明では、前記光照射手段によって照射する光は、前記波長が異なるとともに、その強度又は光量が異なる光であることを特徴とする。
本発明は、光照射手段によって照射する光を例示したものである。
（５）請求項５の発明では、前記波長の異なる光は、緑色光及び赤外光であることを特徴とする。
本発明は、光照射手段によって照射する光を例示したものである。
尚、緑色光の波長としては、４６０ｎｍ〜５７０ｎｍの範囲を採用でき、赤外光の波長としては、７８０ｎｍ〜１０００ｎｍの範囲を採用できる。
【００４３】
【発明の実施の形態】
次に、本発明のセンサの実施の形態の例（実施例）について、図面に基づいて説明する。
（実施例１）
ここでは、センサとして脈波センサを例に挙げるとともに、脈波センサを用いた生体状態検出方法（脈波検出方法）及び生体状態検出装置（脈波検出装置）を例に挙げて説明する。
【００４４】
ａ）まず、本実施例の脈波検出方法を実施する脈波検出装置を、図１に基づいて説明する。
図１に示す様に、本実施例の脈波検出装置１は、人体の脈拍数を検出する装置であり、主として、データ処理装置３と、データ処理装置３に接続された脈波センサ５及び駆動回路７とから構成されている。
【００４５】
このうち、前記データ処理装置３は、脈波センサ５から得られた信号を増幅する検出回路１１と、検出回路１１からの信号をＡ／Ｄ変換するＡＤＣ１３と、ＡＤＣ１３からのデジタル信号を処理して脈波数の検出等の各種の演算処理を行うマイクロコンピュータ１５とを備えている。
【００４６】
前記脈波センサ５は、後に詳述するように、発光素子として、赤外ＬＥＤ１７と緑色ＬＥＤ１９を備えるとともに、受光素子として、フォトダイオード（ＰＤ）２１を備えている。
前記駆動回路７は、赤外ＬＥＤ１７と緑色ＬＥＤ１９とに対して、それぞれ異なるタイミングで赤外光又は緑色光を照射させるための駆動信号を出力する。
【００４７】
尚、データ処理装置３と駆動回路７とは、脈波検出装置本体９の筐体内に収容されている。
ｂ）次に、前記脈波センサ５について、更に詳細に説明する。
前記脈波センサ５は、図２に示す様に、人体の腕等に、約９４０ｎｍの波長の赤外光を照射する赤外ＬＥＤ１７と、約５２０ｎｍの緑色光を照射する緑色ＬＥＤ１９と、人体に照射された赤外光又は緑色光の反射光をそれぞれ受光するＰＤ２１とを備える光学式反射型センサである。
【００４８】
この赤外ＬＥＤ１７、緑色ＬＥＤ１９、ＰＤ２１は、それぞれ脈波センサ５の筐体２３の底部２５に、ＰＤ２１を挟んで左右に赤外ＬＥＤ１７と緑色ＬＥＤ１９とが位置するように並列して配置され、透明な樹脂製の窓２７を介して、赤外光又は緑色光を人体に対して照射できるようにされている。
【００４９】
前記脈波センサ５では、赤外ＬＥＤ１７又は緑色ＬＥＤ１９から人体に向かって光が照射されると、光の一部が人体の内部を通る小・細動脈（毛細動脈）にあたって、毛細動脈を流れる血液中のヘモグロビンに吸収され、残りの光が毛細動脈で反射して散乱し、その一部が受光素子であるＰＤ２１に入射する。この時、血液の脈動により毛細動脈にあるヘモグロビンの量が波動的に変化するので、ヘモグロビンに吸収される光も波動的に変化する。また、血管径の変化によっても、ヘモグロビンの量が変化する。その結果、毛細動脈で反射してＰＤ２１で検出される受光量が変化し、その受光量の変化を脈波情報（例えば電圧信号）としてデータ処理装置３に出力する。
【００５０】
従って、データ処理装置３に入力した（赤外ＬＥＤ１７又は緑色ＬＥＤ１９から照射された光の反射波に対応した）信号（以下検出信号と記す）を用いることにより、後述する様にして、脈拍数等の生体の状態を求めることができる。
尚、図１及び図２では、毛細動脈に照射されて反射する光を点線で示し、皮膚の表面で反射する光を実線で示している。
【００５１】
ｃ）次に、本実施例における脈波検出の原理について説明する。
図３に、データ処理装置３に入力した検出信号を示すが、この検出信号には、毛細動脈に当たって反射した脈波を示す信号（脈波成分）と、皮膚表面又は毛細動脈以外で反射した反射波の成分（反射波成分）との両成分が含まれている。
【００５２】
また、図４に示す様に、前記検出信号を周波数解析することにより、その周波数成分が得られるが、この検出信号を周波数領域で考えると、検出信号には、心拍に同期する脈拍成分と、体動を示す（同期する）体動成分と、（体動成分を除いた反射波成分である）概ね直流成分とが、共に現れる。
【００５３】
このうち、直流成分は、脈拍成分や体動成分とは大きく異なり、検出回路１１などでカットされる（例えば所定の周波数以下をカットするフィルタによりカットされる）ので、以下の説明では省略する。
また、心拍に同期する脈拍成分は脈波に乗り、体動を示す体動成分は脈波と反射波に乗るという特徴がある。
【００５４】
一方、図５（ａ）に示す様に、緑色ＬＥＤ１９を用いた計測において、脈拍成分（実線）と体動成分（点線）とのパワーの比率は、概ね１：５であるが、図５（ｂ）に示す様に、赤外ＬＥＤ１７を用いた計測において、脈拍成分（実線）と体動成分（点線）とのパワーの比率は、概ね１：５０ほどである。
【００５５】
この緑色ＬＥＤ１９と赤外ＬＥＤ１７を用いた場合の特性を踏まえて、本実施例では、赤外ＬＥＤ１７の赤外光の強度を、緑色ＬＥＤ１９の緑色光の強度に比べて、十分小さくしている。ここでは、赤外ＬＥＤ１７の光の強度を、緑色ＬＥＤ１９の光の強度より、約１／５と小さくする。
【００５６】
この光の強度の調節は、赤外ＬＥＤ１７に加える印加電圧を小さくすることにより実現できるが、これ以外に、赤外ＬＥＤ１７として光の強度が小さな定格のＬＥＤを使用することによっても実現できる。
そして、上述した光の強度の調節によって、赤外光の反射波における脈拍成分は、Ｓ（シグナル）／Ｎ（ノイズ）の関係でＮに埋もれてしまい、実質的に検出されなくなるので、体動成分のみが検出されることになる。 尚、赤外ＬＥＤ１７の光の強度を、緑色ＬＥＤ１９の光の強度より、約１／５と小さくすると、体動成分のみの抽出が容易であるので好適である。
【００５７】
よって、緑色ＬＥＤ１９の反射波の（脈拍成分と体動成分を含む）周波数成分から、赤外ＬＥＤ１７の反射波の（体動成分のみを含む）周波数成分とを比較することにより、脈拍成分のみを抽出することができる。
ｄ）次に、本実施例における脈波検出の処理手順について、図６に基づいて説明する。
【００５８】
図６に示す様に、まず、ステップ１００では、（マイクロコンピュータ１５からの制御信号を受けた）駆動回路７により、緑色ＬＥＤ１９を１回発光させる。そして、その反射光をＰＤ２１にて受光し、ＰＤ２１からの（緑色光に対応した）信号を検出回路１１にて増幅し、ＡＤＣ１３を介して、マイクロコンピュータ１５に入力する。
【００５９】
続くステップ１１０では、同様に、緑色ＬＥＤ１９の発光後、赤外ＬＥＤ１７を１回発光させる。そして、その反射光をＰＤ２１にて受光し、ＰＤ２１からの（赤外光に対応した）信号を検出回路１１にて増幅し、ＡＤＣ１３を介して、マイクロコンピュータ１５に入力する。
【００６０】
つまり、緑色ＬＥＤ１９の発光と赤外ＬＥＤ１７の発光とを、サンプリング間隔の５０msec毎に１回づつ交互に発光させるのである（即ち２０Ｈｚ毎に発光させる）。これにより、緑色光と赤外光とが同時にＰＤ２１に受光されないようにする。
【００６１】
特に、赤外ＬＥＤ１７の光の強度を、緑色ＬＥＤ１９の光の強度より、約１／５と十分に小さくする。ここでは、赤外ＬＥＤ１７に加える印加電圧を小さくする。
続くステップ１２０では、後述する周波数解析に必要なデータが得られるように、一定時間（約２５秒）待機し、一定時間経過後に、ステップ１３０に進む。つまり、過去２５秒間の検出信号のデータを周波数解析することにより脈拍成分や体動成分の周波数を求めるので、ここでは、そのためのデータを蓄積するのである。
【００６２】
ステップ１３０では、前記緑色ＬＥＤ１９又は赤外ＬＥＤ１７を用いて得られた各検出信号の周波数解析を行う。
即ち、各検出信号の時系列データに対して周知の高速フーリエ変換（ＦＦＴ）等の周波数解析を実施する。これによって、前記図５に示すような周波数のピーク等のデータが得られる。
【００６３】
続くステップ１４０では、図５（ａ）に示す様に、緑色光に対する（脈拍成分と体動成分を含む）周波数解析結果には有って、図５（ｂ）に示す様に、赤外光に対する（体動成分のみを含む）周波数解析結果に無い周波数、即ち脈拍成分を抽出する。
【００６４】
具体的には、緑色光に対する周波数解析結果から、赤外光に対する周波数解析結果にあるピークの周波数をカットし、残る周波数帯のピークを脈拍成分として抽出する。
続くステップ１５０では、抽出したピークの周波数を脈拍数に換算して、図示しない液晶等のディスプレイに表示する。
【００６５】
具体的には、抽出した周波数に６０秒をかけて脈波数を算出する。例えば周波数が１［Ｈｚ］の場合には、脈拍数は、１［Ｈｚ］×６０［秒］＝６０［拍／分］となる。また、脈拍間隔も、抽出した周波数の逆数を取ることにより算出できる。
【００６６】
続くステップ１６０では、体動成分のみを含む赤外光に対する周波数解析結果から、そのピークの周波数を体動成分に換算して、同様にディスプレイに表示し、一旦本処理を終了する。
具体的には、得られた周波数に６０秒をかけて体動の回数を算出する。
【００６７】
ｅ）ここで、実際に脈波センサ５を人体に装着して運動した場合における検出信号の状態（従って周波数の変化の状態）を、図７に示す。
図７（ａ）に示す様に、緑色ＬＥＤ１９を用いて得られた検出信号を周波数解析した結果、体動成分（点線）と脈拍成分（実線）とによる異なるピークが連続して変化していることが分かる。
【００６８】
一方、図７（ｂ）に示す様に、赤外ＬＥＤ１７を用いて得られた検出信号を周波数解析した結果、体動成分（実線）のみのピークが連続して変化していることが分かる。
従って、このグラフからも、緑色ＬＥＤ１９の反射波の（脈拍成分と体動成分を含む）周波数成分から、赤外ＬＥＤ１７の反射波の（体動成分のみを含む）周波数成分とを比較することにより、脈拍成分のみを抽出して、脈拍数を算出することができること、更には、体動成分も抽出できることが分かる。
【００６９】
この様に、本実施例では、人体に対して、発光タイミングを切り替えて、赤外ＬＥＤ１７からの赤外光の照射と緑色ＬＥＤ１９からの緑色光の照射とを交互に行うとともに、赤外光の強度を緑色光の強度の１／５程度に低減している。そして、各照射光の反射光を受光し、その反射光による信号を周波数解析して、脈拍成分と体動成分とを抽出している。
【００７０】
このとき、赤外光の反射光の周波数解析の結果には、実質的に体動成分しか現れず、また、緑色光の反射光の周波数解析の結果には、脈拍成分と体動成分とが現れるので、両周波数解析の結果を比較することにより、脈拍成分のみを抽出することができる。
【００７１】
そして、脈拍成分から脈拍数や脈拍間隔を求めることができ、体動成分から体動の回数等を求めることができる。
尚、本実施例では、赤外ＬＥＤ１７の光の強度を低減するように調節する場合を例に挙げたが、例えば照射する光量の少ない赤外ＬＥＤを採用するなどの方法により、赤外ＬＥＤ１７の光量を低減するようにしても、同様な効果が得られる。
【００７２】
（実施例２）
次に実施例２の脈波検出装置について説明するが、前記実施例１と同様な箇所の説明は省略する。
本実施例では、赤外ＬＥＤ１７及び緑色ＬＥＤ１９から同じ強度の光を照射する。そして、照射された光の反射光をＰＤ２１にて受光し、検出回路１１にて増幅するが、その増幅率（即ち感度）が赤外ＬＥＤ１７と緑色ＬＥＤ１９とで異なるように調整する。
【００７３】
具体的には、赤外光の反射光による信号の増幅率を、緑色光の反射光による信号の増幅率より十分に小さく（好ましくは１／５程度に）設定する。
これにより、前記実施例１と同様に、赤外ＬＥＤ１７を発光させる場合には、その検出信号における脈拍成分は、Ｓ／Ｎの関係でＮに埋もれて検出されないため、体動成分のみが検出される。よって、同様にして、脈拍成分（即ち脈拍数）や体動成分を求めることができる。
【００７４】
（実施例３）
次に実施例３の脈波検出装置について説明するが、前記実施例１と同様な箇所の説明は省略する。
本実施例では、赤外ＬＥＤ１７及び緑色ＬＥＤ１９から同じ強度の光を照射するとともに、同じ感度で検出信号を増幅する。
【００７５】
つまり、緑色ＬＥＤ１７を用いた場合には、例えば従来の赤外ＬＥＤよりＳ／Ｎが大きいので、赤外ＬＥＤ１７及び緑色ＬＥＤ１９の各検出信号を比較することにより、体動成分のみを抽出することが可能である。
例えば赤外ＬＥＤ１７を用いた場合には、その検出信号の周波数解析の結果において、脈拍成分に対するピークのパワーは小さいので、所定パワー以下の周波数をカットすることにより、体動成分のみを抽出し、更に、前記実施例１と同様にして、心拍成分を抽出することができる。
【００７６】
（実施例４）
次に実施例４の脈波検出装置について説明するが、前記実施例１と同様な箇所の説明は省略する。
本実施例では、図８（ａ）に示す様に、脈波センサ３１は、前記実施例１と同様に、赤外ＬＥＤ３３、緑色ＬＥＤ３５、ＰＤ３７を備えるが、特に、赤外ＬＥＤ３３の上部の窓（即ち透明の樹脂製の窓部材）３９の一部が切り欠かれて、引き下がり部に相当する凹部４１が形成されている。
【００７７】
つまり、この凹部４１により、窓３９の上面４３は人体に直接接触しないようにされているので、皮膚の表面は体動に伴って揺れやすくなり、体動を強調して検出することができる。
よって、赤外ＬＥＤ３３の強度（又は光量）を小さくでき、消費電力を節約することができる。
【００７８】
尚、これとは別に、図示しないが、赤外ＬＥＤの上部の窓に凹凸を設けてよい。この方法でも、体動を強調して取り出すことができる。
（実施例５）
次に実施例５の脈波検出装置について説明するが、前記実施例１と同様な箇所の説明は省略する。
【００７９】
本実施例では、図８（ｂ）に示す様に、脈波センサ５１は、前記実施例４と同様に、赤外ＬＥＤ５３、緑色ＬＥＤ５５、ＰＤ５７を備え、赤外ＬＥＤ５３の上部の窓５９の一部が切り欠かれて、凹部６１が形成されている。
特に本実施例では、この凹部６１に、透明で柔軟な材料（例えばゲル状のシリコン）からなる表面層６３が配置されている。
【００８０】
よって、本実施例においても、皮膚の表面は体動に伴って揺れやすくなり、体動を強調して検出することができるので、赤外ＬＥＤ５３の強度（又は光量）を小さくでき、消費電力を節約することができる。
（実施例６）
次に実施例６の脈波検出装置について説明するが、前記実施例１と同様な箇所の説明は省略する。
【００８１】
図９に示す様に、本実施例の脈波センサ７１は、２対の素子を備えている。
具体的には、赤外ＬＥＤ７３と、その反射光を受光する赤外用ＰＤ７５と、緑色ＬＥＤ７７と、その反射光を受光する緑色用ＰＤ７９とを備えている。
そして、各素子対の領域を遮蔽して分離するために、各素子対の間には、光を通さない材料からなる分離壁８１が設けられている。
【００８２】
本実施例は、前記実施例１と同様な効果を奏するとともに、各素子対は光学的に分離されているので、赤外ＬＥＤ７３及び緑色ＬＥＤ７７から同時に光を照射することができる。
よって、処理時間を節約できるという利点がある。
【００８３】
尚、本発明は前記実施例になんら限定されるものではなく、本発明を逸脱しない範囲において種々の態様で実施しうることはいうまでもない。
（１）例えば、前記実施例では、脈波検出装置について述べたが、脈拍成分や体動成分を抽出する処理等に関しては、上述したアルゴリズムに基づく処理を実行させるプログラムやそのプログラムを記憶している記録媒体にも適用できる。
【００８４】
この記録媒体としては、マイクロコンピュータとして構成される電子制御装置、マイクロチップ、フレキシブルディスク、ハードディスク、ＤＶＤ、光ディスク等の各種の記録媒体が挙げられる。つまり、上述した脈波検出装置の処理を実行させることができるプログラムを記憶したものであれば、特に限定はない。
【００８５】
尚、前記プログラムは、単に記録媒体に記憶されたものに限定されることなく、例えばインターネットなどの通信ラインにて送受信されるプログラムにも適用される。
（２）また、前記脈波検出装置は、脈波センサから得られた信号を、すぐそばにあるデータ処理装置に直接に入力する場合だけでなく、脈波センサからの得られたデータを例えばパソコン等の装置に入力し、そのデータを例えばインターネット等を利用して遠隔地にあるデータ処理装置に送信にして、脈拍成分（従って脈拍数）や体動成分を測定する場合に適用することもできる。
【図面の簡単な説明】
【図１】 実施例１の脈波検出装置の主要な構成を示す説明図である。
【図２】 実施例１の脈波センサの使用方法等を示す説明図である。
【図３】 実施例１の脈波センサによって得られる検出信号を示すグラフである。
【図４】 実施例１の検出信号の周波数解析の結果を模式的に示すグラフである。
【図５】 実施例１の検出信号の周波数解析の結果を模式的に示すグラフであり、（ａ）は緑色光に関する周波数解析結果を示すグラフ、（ｂ）は赤外光に関する周波数解析結果を示すグラフである。
【図６】 実施例１の脈波検出処理を示すフローチャートである。
【図７】 実際の検出信号の周波数解析の結果を示すグラフであり、（ａ）は緑色光に関する周波数解析結果を示すグラフ、（ｂ）は赤外光に関する周波数解析結果を示すグラフである。
【図８】 （ａ）は実施例４の脈波センサを示す説明図、（ｂ）は実施例５の脈波センサを示す説明図である。
【図９】 実施例６の脈波センサを示す説明図である。
【図１０】 従来技術の説明図である。
【符号の説明】
１…脈波検出装置
３…データ処理装置部
５、３１、５１、７１…脈波センサ
７…駆動回路
１７、３３、５５、７３…赤外ＬＥＤ
１９、３５、５７、７７…緑色ＬＥＤ
２１、３７、５９、７５、７９…フォトダイオード（ＰＤ）
２７…窓[0001]
BACKGROUND OF THE INVENTION
The present invention relates to a sensor that detects a state of a living body such as a pulse rate.
[0002]
[Prior art]
In recent years, there has been a growing need for monitoring the heart rate (heart rate) in daily life and during exercise such as jogging for health management purposes. In order to detect this heart rate, a general method is to measure the action potential generated with the heartbeat from the chest, that is, to calculate from the peak interval time of the amplitude using an electrocardiogram.
[0003]
However, this method requires electrodes to be attached to the body, and the procedure is cumbersome. Recently, as a simpler method, a method of measuring the pulse wave and detecting the pulse rate has been considered.
The pulse wave is a pressure fluctuation in an artery that occurs as a heart beat is transmitted to a peripheral artery as a wave, and an optical pulse wave sensor is used as a device for measuring the pulse wave.
[0004]
This optical pulse wave sensor measures the volumetric volume change of blood in peripheral arteries using the light absorption characteristics of hemoglobin in the blood, and can be easily applied to the human body (finger, arm, temple, etc.) Since it is possible to measure the pulse wave by wearing it, it is considered that the device will be widely used in the future as a device for detecting the pulse rate.
[0005]
The heart rate and the pulse rate (beats / minute) are values obtained by dividing 60 by the peak interval time (seconds) of the amplitude of the electrocardiogram waveform and the pulse wave waveform, as shown in the following formula (1). .
Heart rate, pulse rate (beats / minute) = 60 / peak interval time (seconds) of amplitude (1)
As shown in FIG. 10, the peak positions of the amplitudes of the electrocardiogram waveform and the pulse wave waveform are normally synchronized, and the heart rate and the pulse rate coincide with each other.
[0006]
However, during daily life and exercise, if body movement occurs at the measurement site where the pulse wave sensor is attached, the blood flow of the peripheral artery is disturbed, and the peak of the amplitude of the pulse wave unrelated to the heartbeat occurs. Pulse rate will not match. If this happens, the original purpose of using the pulse rate as a substitute for the heart rate cannot be achieved.
[0007]
In addition, since the peak of the amplitude of the pulse wave that is not related to the heartbeat is close to the frequency of the peak of the amplitude of the pulse wave that is synchronized with the heartbeat, there is a countermeasure in the filter processing applied to normal noise removal. Impossible.
As a countermeasure against this, a technique has been proposed in which a signal due to motion noise is detected using a motion noise sensor, motion noise is removed from a signal that is a combination of motion noise and a pulse signal, and an accurate pulse is detected even during motion. (See Patent Document 1).
[0008]
In addition, there is a technology that distinguishes between body motion wave components and blood pulsation wave components of a living body by irradiating a living body with light of different wavelengths and processing the signals obtained by each to detect the pulse accurately. It has been proposed (see Patent Document 2).
[0009]
[Patent Document 1]
JP 7-299044 A (2nd page, FIG. 1)
[Patent Document 2]
Japanese Patent Laid-Open No. 7-088092 (second page, FIG. 1)
[0010]
[Problems to be solved by the invention]
However, the technique of
[0011]
In the technique of Patent Document 2, the body motion wave component and the blood pulsation wave component are included in both signals, and the relationship between the body motion wave component and the blood pulsation wave component depends on the wearing state of the sensor and individual differences. Therefore, there is a problem that the pulse cannot be accurately obtained by the unique calculation process described in the publication.
The present invention has been made to solve the above-mentioned problems, and its purpose is to reduce the influence of skin surface reflection, sensor mounting state, individual differences, etc., and accurately determine the state of a living body such as a pulse. It is to provide a sensor that can detect.
[0033]
[Means for Solving the Problems and Effects of the Invention]
(1) The invention of
[0034]
In the present invention, the outer skin of the long-wavelength light (for example, infrared light) and / or the outer window of the long-wavelength light receiving side is separated from the human skin. Since a pull-down portion (portion serving as a gap) is provided on the skin, the movement of the skin is facilitated as compared with a portion where the skin is in close contact with the outside of the window portion. Therefore, for example, when infrared light is used, there is an effect that the ability to detect a change in body movement is high.
[0035]
(2) The invention of claim 2 is directed to a light irradiating means for separately irradiating a living body with light having different wavelengths, and a reflected wave light receiving for receiving reflected light of each light emitted from the light irradiating means. In a sensor (for example, a pulse wave sensor) housed in a housing, a window through which each light and its reflected light is transmitted to the light irradiation side and the light receiving side of each of the light irradiation means and the reflected wave light receiving means And an unevenness provided on the outside of the window on the side that irradiates the long wavelength light and / or on the outside of the window on the side that receives the reflected wave of the long wavelength light. The gist of the sensor.
[0036]
In the present invention, since the projections and depressions are provided on the outside of the window on the side that irradiates long wavelength light (for example, infrared light) and / or on the outside of the window on the side that receives the reflected wave of long wavelength light, The movement of the skin is facilitated as compared with the part where the skin is in close contact with the outside of the part. Therefore, for example, when infrared light is used, there is an effect that the ability to detect a change in body movement is high.
[0037]
(3) The invention of claim 3 is a light irradiation means for separately irradiating light with different wavelengths to a living body, and a reflected wave reception for receiving reflected light of each light emitted from the light irradiation means. In a sensor (for example, a pulse wave sensor) housed in a housing, a window through which each light and its reflected light is transmitted to the light irradiation side and the light receiving side of each of the light irradiation means and the reflected wave light receiving means And a translucent flexible material is disposed on the outside of the window on the side irradiating the long wavelength light and / or on the outside of the window on the side receiving the reflected wave of the long wavelength light. The gist of the sensor is as follows.
[0038]
In the present invention, on the outside of the window portion on the side that irradiates the long wavelength light (for example, infrared light) and / or on the outside of the window portion on the side that receives the reflected wave of the long wavelength light, the light-transmitting flexible Since the member made of the material is disposed, the movement of the skin is facilitated as compared with the portion where the skin is in close contact with the outside of the hard window portion. Therefore, for example, when infrared light is used, there is an effect that the ability to detect a change in body movement is high.
[0039]
(4) The invention of claim 4 is characterized in that the light irradiated by the light irradiation means is light having different wavelengths and different intensities or light amounts.
The present invention exemplifies light irradiated by the light irradiation means.
(5) The invention according to
The present invention exemplifies light irradiated by the light irradiation means.
The green light wavelength can be in the range of 460 nm to 570 nm, and the infrared light wavelength can be in the range of 780 nm to 1000 nm.
[0043]
DETAILED DESCRIPTION OF THE INVENTION
Next, an example (example) of an embodiment of the sensor of the present invention will be described based on the drawings.
Example 1
Here, a pulse wave sensor is taken as an example of the sensor, and a living body state detecting method (pulse wave detecting method) and a living body state detecting device (pulse wave detecting device) using the pulse wave sensor are described as examples .
[0044]
a) First, a pulse wave detection apparatus that implements the pulse wave detection method of this embodiment will be described with reference to FIG.
As shown in FIG. 1, the pulse
[0045]
Among these, the data processing device 3 processes the
[0046]
As will be described in detail later, the
The drive circuit 7 outputs drive signals for irradiating the infrared LED 17 and the green LED 19 with infrared light or green light at different timings.
[0047]
The data processing device 3 and the drive circuit 7 are housed in the casing of the pulse wave detection device main body 9.
b) Next, the
As shown in FIG. 2, the
[0048]
The infrared LED 17, the green LED 19, and the PD 21 are arranged in parallel on the bottom 25 of the
[0049]
In the
[0050]
Accordingly, by using a signal (corresponding to a reflected wave of light emitted from the infrared LED 17 or the green LED 19) (hereinafter referred to as a detection signal) input to the data processing device 3, as described later, the pulse rate and the like The state of the living body can be obtained.
In FIG. 1 and FIG. 2, the light that is applied to the capillary artery and reflected is indicated by a dotted line, and the light that is reflected by the surface of the skin is indicated by a solid line.
[0051]
c) Next, the principle of pulse wave detection in this embodiment will be described.
FIG. 3 shows a detection signal input to the data processing device 3. This detection signal includes a signal (pulse wave component) indicating a pulse wave reflected on the capillary artery and a reflection reflected on the skin surface or other than the capillary artery. Both components of wave components (reflected wave components) are included.
[0052]
Further, as shown in FIG. 4, the frequency component of the detection signal can be obtained by frequency analysis of the detection signal. When the detection signal is considered in the frequency domain, the detection signal includes a pulse component synchronized with the heartbeat, A body motion component indicating (synchronizing) body motion and a substantially direct current component (which is a reflected wave component excluding the body motion component) appear together.
[0053]
Among them, the direct current component is greatly different from the pulse component and the body motion component, and is cut by the
Further, there is a feature that a pulse component synchronized with a heartbeat rides on a pulse wave, and a body motion component indicating body motion rides on a pulse wave and a reflected wave.
[0054]
On the other hand, as shown in FIG. 5A, in the measurement using the green LED 19, the power ratio between the pulse component (solid line) and the body motion component (dotted line) is approximately 1: 5. As shown in b), in the measurement using the infrared LED 17, the power ratio between the pulse component (solid line) and the body motion component (dotted line) is about 1:50.
[0055]
In the present embodiment, the intensity of the infrared light of the infrared LED 17 is made sufficiently smaller than the intensity of the green light of the green LED 19 based on the characteristics when the green LED 19 and the infrared LED 17 are used. Here, the intensity of the light of the infrared LED 17 is set to about 1/5 that of the light of the green LED 19.
[0056]
The adjustment of the light intensity can be realized by reducing the applied voltage applied to the infrared LED 17, but it can also be realized by using a rated LED having a low light intensity as the infrared LED 17.
By adjusting the intensity of light as described above, the pulse component in the reflected wave of infrared light is buried in N due to the relationship of S (signal) / N (noise), and is not substantially detected. Only the component will be detected. Note that it is preferable to make the light intensity of the infrared LED 17 about 1/5 smaller than the light intensity of the green LED 19 because it is easy to extract only body motion components.
[0057]
Therefore, by comparing the frequency component of the reflected wave of the green LED 19 (including the pulse component and the body motion component) with the frequency component of the reflected wave of the infrared LED 17 (including only the body motion component), only the pulse component is obtained. Can be extracted.
d) Next, the processing procedure of pulse wave detection in the present embodiment will be described with reference to FIG.
[0058]
As shown in FIG. 6, first, in
[0059]
In
[0060]
That is, the light emitted from the green LED 19 and the light emitted from the infrared LED 17 are alternately emitted once every 50 msec of the sampling interval (that is, emitted every 20 Hz). This prevents green light and infrared light from being simultaneously received by the PD 21.
[0061]
In particular, the intensity of the light of the infrared LED 17 is made sufficiently lower to about 1/5 than the intensity of the light of the green LED 19. Here, the applied voltage applied to the infrared LED 17 is reduced.
In the
[0062]
In step 130, frequency analysis of each detection signal obtained using the green LED 19 or the infrared LED 17 is performed.
That is, a frequency analysis such as a well-known fast Fourier transform (FFT) is performed on the time series data of each detection signal. As a result, data such as frequency peaks as shown in FIG. 5 is obtained.
[0063]
In the
[0064]
Specifically, the peak frequency in the frequency analysis result for infrared light is cut from the frequency analysis result for green light, and the remaining frequency band peak is extracted as a pulse component.
In the
[0065]
Specifically, the pulse wave number is calculated by taking 60 seconds for the extracted frequency. For example, when the frequency is 1 [Hz], the pulse rate is 1 [Hz] × 60 [seconds] = 60 [beats / minute]. The pulse interval can also be calculated by taking the reciprocal of the extracted frequency.
[0066]
In the
Specifically, the number of body movements is calculated by taking 60 seconds for the obtained frequency.
[0067]
e) FIG. 7 shows the state of the detection signal when the
As shown in FIG. 7A, as a result of frequency analysis of the detection signal obtained using the green LED 19, different peaks due to the body motion component (dotted line) and the pulse component (solid line) continuously change. I understand that.
[0068]
On the other hand, as shown in FIG. 7B, as a result of frequency analysis of the detection signal obtained using the infrared LED 17, it can be seen that only the peak of the body motion component (solid line) changes continuously.
Therefore, also from this graph, by comparing the frequency component of the reflected wave of the green LED 19 (including the pulse component and the body motion component) with the frequency component of the reflected wave of the infrared LED 17 (including only the body motion component). It can be seen that only the pulse component can be extracted to calculate the pulse rate, and that the body motion component can also be extracted.
[0069]
As described above, in this embodiment, the light emission timing is switched for the human body, and the infrared light irradiation from the infrared LED 17 and the green light irradiation from the green LED 19 are alternately performed, and the infrared light is emitted. The intensity is reduced to about 1/5 of the intensity of green light. And the reflected light of each irradiation light is received, the signal by the reflected light is frequency-analyzed, and the pulse component and the body motion component are extracted.
[0070]
At this time, only the body motion component appears in the result of the frequency analysis of the reflected light of the infrared light, and the pulse component and the body motion component are included in the result of the frequency analysis of the reflected light of the green light. Since it appears, only the pulse component can be extracted by comparing the results of both frequency analyses.
[0071]
And a pulse rate and a pulse interval can be calculated | required from a pulse component, and the frequency | count of a body motion etc. can be calculated | required from a body motion component.
In the present embodiment, the case of adjusting the light intensity of the infrared LED 17 to be reduced was described as an example. However, the infrared LED 17 can be adjusted by a method such as adopting an infrared LED with a small amount of light to be irradiated. Even if the amount of light is reduced, the same effect can be obtained.
[0072]
(Example 2)
Next, the pulse wave detection device of the second embodiment will be described, but the description of the same parts as those of the first embodiment will be omitted.
In this embodiment, the infrared LED 17 and the green LED 19 emit light having the same intensity. The reflected light of the irradiated light is received by the PD 21 and amplified by the
[0073]
Specifically, the amplification factor of the signal by the reflected light of the infrared light is set sufficiently smaller (preferably about 1/5) than the amplification factor of the signal by the reflected light of the green light.
Thus, as in the first embodiment, when the infrared LED 17 is caused to emit light, the pulse component in the detection signal is buried in N due to the S / N relationship and is not detected, so only the body motion component is detected. The Therefore, similarly, a pulse component (that is, a pulse rate) and a body motion component can be obtained.
[0074]
Example 3
Next, the pulse wave detection device of the third embodiment will be described, but the description of the same parts as those of the first embodiment will be omitted.
In this embodiment, the infrared LED 17 and the green LED 19 emit light having the same intensity, and the detection signal is amplified with the same sensitivity.
[0075]
That is, when the green LED 17 is used, for example, since the S / N is larger than that of the conventional infrared LED, it is possible to extract only the body movement component by comparing the detection signals of the infrared LED 17 and the green LED 19. Is possible.
For example, when the infrared LED 17 is used, in the result of the frequency analysis of the detection signal, the peak power with respect to the pulse component is small, so by cutting the frequency below the predetermined power, only the body motion component is extracted, Further, the heartbeat component can be extracted in the same manner as in the first embodiment.
[0076]
(Example 4)
Next, the pulse wave detection device of the fourth embodiment will be described, but the description of the same parts as those of the first embodiment will be omitted.
In this embodiment, as shown in FIG. 8A, the
[0077]
In other words, the
Therefore, the intensity (or light amount) of the
[0078]
Apart from this, although not shown in the drawings, the upper window of the infrared LED may be provided with irregularities. Even with this method, body movement can be emphasized and extracted.
(Example 5)
Next, the pulse wave detection device of the fifth embodiment will be described, but the description of the same parts as those of the first embodiment will be omitted.
[0079]
In this embodiment, as shown in FIG. 8B, the
Particularly in the present embodiment, a
[0080]
Therefore, also in the present embodiment, the skin surface easily shakes with body movement, and the body movement can be emphasized and detected, so that the intensity (or light quantity) of the infrared LED 53 can be reduced, and the power consumption can be reduced. Can be saved.
(Example 6)
Next, the pulse wave detection device of the sixth embodiment will be described, but the description of the same parts as those of the first embodiment will be omitted.
[0081]
As shown in FIG. 9, the
Specifically, it includes an
And in order to shield and isolate | separate the area | region of each element pair, between each element pair, the isolation | separation wall 81 which consists of material which does not permeate | transmit light is provided.
[0082]
The present embodiment has the same effect as the first embodiment, and each element pair is optically separated. Therefore, the
Therefore, there is an advantage that processing time can be saved.
[0083]
Needless to say, the present invention is not limited to the above-described embodiments, and can be implemented in various modes without departing from the scope of the present invention.
(1) For example, in the above-described embodiment, the pulse wave detection device has been described. However, with respect to the processing for extracting the pulse component and the body motion component, a program for executing the processing based on the above-described algorithm and the program are stored. It can also be applied to existing recording media.
[0084]
Examples of the recording medium include various recording media such as an electronic control device configured as a microcomputer, a microchip, a flexible disk, a hard disk, a DVD, and an optical disk. That is, there is no particular limitation as long as it stores a program that can execute the processing of the pulse wave detection device described above.
[0085]
The program is not limited to a program stored in a recording medium, but can be applied to a program transmitted / received through a communication line such as the Internet.
(2) Further, the pulse wave detection device not only directly inputs a signal obtained from the pulse wave sensor to a data processing device nearby, but also obtains data obtained from the pulse wave sensor, for example. It can also be applied when measuring pulse components (thus pulse rate) and body motion components by inputting to a device such as a personal computer and transmitting the data to a remote data processing device using the Internet, for example. it can.
[Brief description of the drawings]
FIG. 1 is an explanatory diagram illustrating a main configuration of a pulse wave detection device according to a first embodiment.
FIG. 2 is an explanatory diagram illustrating a usage method and the like of the pulse wave sensor according to the first embodiment.
3 is a graph showing detection signals obtained by the pulse wave sensor of Example 1. FIG.
4 is a graph schematically showing a result of frequency analysis of a detection signal of Example 1. FIG.
5A and 5B are graphs schematically showing the results of frequency analysis of detection signals in Example 1. FIG. 5A is a graph showing the frequency analysis results for green light, and FIG. 5B is the frequency analysis result for infrared light. It is a graph to show.
FIG. 6 is a flowchart illustrating a pulse wave detection process according to the first embodiment.
7A and 7B are graphs showing the results of frequency analysis of actual detection signals, where FIG. 7A is a graph showing the results of frequency analysis for green light, and FIG. 7B is a graph showing the results of frequency analysis for infrared light.
8A is an explanatory diagram showing a pulse wave sensor of Example 4, and FIG. 8B is an explanatory diagram showing a pulse wave sensor of Example 5. FIG.
FIG. 9 is an explanatory diagram showing a pulse wave sensor according to a sixth embodiment.
FIG. 10 is an explanatory diagram of a conventional technique.
[Explanation of symbols]
DESCRIPTION OF
19, 35, 57, 77 ... Green LED
21, 37, 59, 75, 79 ... Photodiode (PD)
27 ... window
Claims (5)
前記光照射手段から照射された各光の反射光を受光する反射波受光手段と、
を、筐体内に収容したセンサにおいて、
前記光照射手段及び前記反射波受光手段の各光の照射側及び受光側に、各光及びその反射光が透過する窓部を備えるとともに、前記長波長の光を照射する側の窓部の外側及び／又は前記長波長の光の反射波を受光する側の窓部の外側に、前記人体の皮膚から離すように引き下がり部を設けたことを特徴とするセンサ。 A light irradiating means for separately irradiating the living body with light having different wavelengths;
Reflected wave light receiving means for receiving reflected light of each light emitted from the light irradiating means;
In a sensor housed in a housing,
The light irradiating means and the reflected wave light receiving means are provided on the light irradiation side and the light receiving side with a window portion through which each light and its reflected light are transmitted, and outside the window portion on the side where the long wavelength light is irradiated And / or a sensor having a pull-down portion outside the window on the side receiving the reflected wave of the long-wavelength light so as to be separated from the skin of the human body.
前記光照射手段から照射された各光の反射光を受光する反射波受光手段と、 Reflected wave light receiving means for receiving reflected light of each light emitted from the light irradiating means;
を、筐体内に収容したセンサにおいて、 In a sensor housed in a housing,
前記光照射手段及び前記反射波受光手段の各光の照射側及び受光側に、各光及びその反射光が透過する窓部を備えるとともに、前記長波長の光を照射する側の窓部の外側及び／又は前記長波長の光の反射波を受光する側の窓部の外側に、凹凸を設けたことを特徴とするセンサ。 The light irradiating means and the reflected wave light receiving means are provided on the light irradiation side and the light receiving side with a window portion through which each light and its reflected light are transmitted, and outside the window portion on the side where the long wavelength light is irradiated. And / or a sensor provided with irregularities on the outside of the window on the side of receiving the reflected wave of the light having the long wavelength.
前記光照射手段から照射された各光の反射光を受光する反射波受光手段と、 Reflected wave light receiving means for receiving reflected light of each light emitted from the light irradiating means;
を、筐体内に収容したセンサにおいて、 In a sensor housed in a housing,
前記光照射手段及び前記反射波受光手段の各光の照射側及び受光側に、各光及びその反射光が透過する窓部を備えるとともに、前記長波長の光を照射する側の窓部の外側及び／又は前記長波長の光の反射波を受光する側の窓部の外側に、透光性の柔軟な材料を配置したことを特徴とするセンサ。 The light irradiating means and the reflected wave light receiving means are provided on the light irradiation side and the light receiving side with a window portion through which each light and its reflected light are transmitted, and outside the window portion on the side where the long wavelength light is irradiated. And / or a light-transmitting flexible material disposed outside the window on the side of receiving the reflected wave of the long-wavelength light.
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| JP2003054581A JP3760920B2 (en) | 2003-02-28 | 2003-02-28 | Sensor |
| US10/786,156 US7252639B2 (en) | 2003-02-28 | 2004-02-26 | Method and apparatus for measuring biological condition |
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Also Published As
| Publication number | Publication date |
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| US7252639B2 (en) | 2007-08-07 |
| JP2004261366A (en) | 2004-09-24 |
| US20040193063A1 (en) | 2004-09-30 |
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